Membrane separation devices, systems and methods employing same and data management systems and methods

ABSTRACT

A membrane separation device for use in blood processing procedures is disclosed. In one embodiment, a spinning membrane separator is provided in which at least two zones or regions are created in the gap between the spinning membrane and the shell, such that mixing of the fluid between the two regions is inhibited by a radial rib or ridge associated with the spinning membrane that decreases the gap between the spinning membrane and the shell to define two fluid regions, the ridge isolating the fluid in the two regions to minimize mixing between the two. Automated systems and methods are disclosed for separating a unit of previously collected whole blood into selected blood components, such as concentrated red cells and plasma, for collecting red cells and plasma directly from a donor in a single pass, and for cell washing. Data management systems and methods and priming methods are also disclosed.

CROSS REFERENCE TO RELATED APPLICATIONS

This application claims the benefit of the filing dates of U.S. Provisional Application Ser. Nos. 61/451,903, filed Mar. 11, 2011, 61/537,856, filed Sep. 22, 2011, 61/538,558, filed Sep. 23, 2011, and 61/550,516, filed Oct. 24, 2011, the entire contents of each being incorporated herein by reference.

FIELD OF THE DISCLOSURE

The present application is related, in part, to separation devices of the type employing relatively rotating surfaces, at least one of which carries a membrane for filtering a component from fluid passed between the surfaces; to fluid flow circuits and systems incorporating such a separator; and to the use of such systems to separate biological cells, such as red cells, plasma or white cells, from whole blood, a storage medium, a suspension medium, a supernatant, or the like.

BACKGROUND

Traditional blood collection continues to rely heavily on manual collection of whole blood from healthy donors through blood drives, from donor visits to blood centers or hospitals and the like. In typical manual collection, whole blood is collected by simply flowing it, under the force of gravity and venous pressure, from the vein of the donor into a collection container. The amount of whole blood drawn is typically a “unit,” which is about 450 ml.

More specifically, such a collection typically employs a pre-assembled arrangement of tubing and containers or bags, including a flexible plastic primary container or bag for receiving a unit of whole blood from a donor and one or more “satellite” containers or bags. The blood is first collected in the primary container, which also contains an anticoagulant (typically containing sodium citrate, phosphate and dextrose—often referred to as CPD). A preservative (often called an “additive solution” or AS, and commonly containing a saline, adenine and glucose medium—which is referred to as SAG) may be included as part of a larger assembly of bags and tubes that are used in processing after the blood is collected.

After collection of a unit of whole blood, it is common practice in blood banking to transport the unit of whole blood, with connected tubing and containers, to a blood component processing laboratory, commonly referred to as a “back lab,” for further processing. Further processing usually entails manually loading the primary container and associated tubing and satellite containers into a centrifuge to separate the whole blood into components such as concentrated red cells and platelet-rich or platelet-poor plasma. These components are then manually expressed from the primary container into other pre-connected satellite containers, and may be again centrifuged to separate the platelets from plasma. Subsequently, the blood components may be leukoreduced by filtration for further processing or storage. In short, this process is time consuming, labor intensive, and subject to possible human error.

Another routine task performed by blood banks and transfusion center is “cell washing.” This may be performed to remove and/or replace the liquid medium (or a part thereof) in which the cells are suspended, to concentrate or further concentrate cells in a liquid medium, and/or to purify a cell suspension by the removal of unwanted cellular or other material.

Previous cell washing systems most typically involved centrifugation of a cell-suspension, decanting of the supernatant, re-suspension of concentrated cells in new media, and possible repetition of these steps until the cells of the suspension are provided at an adequately high or otherwise desirable concentration. Centrifugal separators used in the processing of blood and blood components have commonly been used in such cell-washing methods.

These processes are also quite time consuming, requiring repeated manual manipulation of the blood or blood components and assembly or disassembly of various fluid processing apparatus. This, of course, increases not only the costs, but the potential for human error or mistake. Accordingly, despite decades of advancement in blood separation devices and processes, there continues to be a desire for better and/or more efficient separation devices, systems and methods applicable to basic blood collection and processing modalities.

While many of the prior blood separation apparatus and procedures have employed centrifugal separation principles, there is another class of devices, based on the use of a membrane, that has been used for plasmapheresis, that is separating plasma from whole blood. More specifically, this type of device employs relatively rotating surfaces, at least one or which carries a porous membrane. Typically the device employs an outer stationary housing and an internal spinning rotor covered by a porous membrane.

One such well-known plasmapheresis device is the Autopheresis-C® separator sold by Fenwal, Inc. of Lake Zurich, Ill. A detailed description of a spinning membrane separator may be found in U.S. Pat. No. 5,194,145 to Schoendorfer, which is incorporated by reference herein. This patent describes a membrane-covered spinner having an interior collection system disposed within a stationary shell. Blood is fed into an annular space or gap between the spinner and the shell. The blood moves along the longitudinal axis of the shell toward an exit region, with plasma passing through the membrane and out of the shell into a collection bag. The remaining blood components, primarily red blood cells, platelets and white cells, move to the exit region between the spinner and the shell and then are typically returned to the donor.

Spinning membrane separators have been found to provide excellent plasma filtration rates, due primarily to the unique flow patterns (“Taylor vortices”) induced in the gap between the spinning membrane and the shell. The Taylor vortices help to keep the blood cells from depositing on and fouling or clogging the membrane.

While spinning membrane separators have been widely used for the collection of plasma, they have not typically been used for the collection of other blood components, specifically red blood cells. Spinning membrane separators also have not typically been used for cell washing. One example of a spinning membrane separator used in the washing of cells such as red blood cells is described in U.S. Pat. No. 5,053,121 which is also incorporated by reference in its entirety. However, the system described therein utilizes two separate spinners associated in series or in parallel to wash “shed” blood of a patient. Other descriptions of the use of spinning membrane separators for separation of blood or blood components may also be found in U.S. Pat. Nos. 5,376,263; 4,776,964; 4,753,729; 5,135,667 and 4,755,300.

The subject matter disclosed herein provides further advances in membrane separators, potential cost reduction and various other advances and advantages over the prior manual collection and processing of blood.

SUMMARY OF THE DISCLOSURE

The present subject matter has a number of aspects which may be used in various combinations, and the disclosure of one or more specific embodiments is for the purpose of disclosure and description, and not limitation. This summary highlights only a few of the aspects of this subject matter, and additional aspects are disclosed in the drawings and the more detailed description that follows.

By way of the present disclosure, a membrane separator is provided that more efficiently separates whole blood into its components and may be advantageously used in various blood processing systems and procedures.

In particular, a blood filtration device is provided having a generally cylindrical housing with an interior wall and an interior member mounted interior of the housing and having an external surface. The interior wall of the housing and/or the external surface of the interior member include a porous membrane spaced apart from the facing wall of the housing or surface of the interior member so as to define an annular gap therebetween, with the housing and interior member being relatively rotatable. An inlet is provided for directing whole blood comprising plasma and red cells into the annular gap, while a second outlet is provided for directing from the annular gap the remaining blood components. The membrane has a surface area sufficient to separate plasma at a flow rate resulting in the residence time of the red blood cells within the annular gap being insufficient to cause undue hemolysis of red blood cells. In one embodiment, this is accomplished by providing an interior member that has a length and/or diameter greater than the length and diameter of the interior members of the prior art devices. More specifically, an interior member according to the present application comprises a rotor that has a length of up to 2.5 times the length of the rotors of the prior spinning membrane devices and a diameter of up to 2.0 times the diameter of the rotors of prior spinning membrane devices. Such separators have been found to provide improved plasma separation rates and also acceptably low levels of hemolysis in the retained blood. In one particular embodiment, the length of the inner member is about 5.51″ and the diameter is about 1.5″.

A method for designing such a membrane separation device is also disclosed. The method includes developing a model utilizing inputs obtained semi-empirically from an existing filtration device having a porous membrane of specified dimensions to obtain specified outputs. The model is applied to hypothetical filtration devices having membranes of varying dimensions so as to obtain predicted values for the specified outputs. The predicted values are reviewed, and membrane dimensions are selected based on a comparison of the predicted values of the specified outputs. In one aspect, the method provides a membrane surface area that enhances one or more filtration characteristics. In a particular example, the filtration device comprises an inner member having the membrane mounted thereto, the inner member being mounted for rotation relative to a generally cylindrical housing, and the inner member having a diameter and/or membrane length to allow filtration without undue lysis to the red blood cells in the blood. In a specific application of the model, the inner member has a diameter of up to about 2.0 times the diameter of the inner member of existing filtration devices and/or a membrane length of up to about 2.5 times the membrane length of existing filtration devices.

In another aspect of the disclosure, a membrane separator is provided in which at least two zones or regions are created in the gap between the interior member and the shell, such that mixing of the fluid between the two regions is inhibited. More particularly, a membrane separator is provided in which either the interior wall of the outer structure and/or the external surface of the inner structure includes a radial rib or ridge that decreases the gap between the two surfaces to define two fluid regions, the ridge isolating the fluid in the two regions to minimize mixing between the two.

BRIEF DESCRIPTION OF THE DRAWINGS

These and other features of the present subject matter are described in the following detailed description and shown in the attached figures, of which:

FIG. 1 is a perspective view a spinning membrane separator, in partial cross section and with portions removed to show detail.

FIG. 2 is a longitudinal cross sectional view of the spinning membrane separator of FIG. 1.

FIG. 3 is a contour plot of outlet hematocrit and outlet wall shear stress as a function of relative filtration length and spinner radius based on a theoretical design model.

FIG. 4 is a contour plot of outlet hematocrit and outlet plasma hemoglobin concentration as a function of relative filtration length and spinner radius based on a theoretical design model for which the membrane tangential velocity is constant.

FIG. 5 is a contour plot of outlet hematocrit and Taylor number as a function of relative filtration length and spinner radius based on a theoretical design model.

FIG. 6 is a three-dimensional plot of plasma hemoglobin concentration as a function of relative filtration length and spinner radius based on a theoretical design model.

FIG. 7 is a perspective view of a spinning membrane device or separator according to the present application.

FIG. 8 is a schematic cross sectional view of a spinning membrane separator in accordance with the present application in which the spinner includes a radially-extending ridge for defining separate fluid regions.

FIG. 9 is a schematic view of an automated whole blood separation system for processing previously-collected whole blood including a disposable fluid flow circuit module and a durable controller or control module with the fluid flow circuit module assembled thereon.

FIG. 10 is a flow diagram showing one embodiment of fluid flow through a fluid flow circuit as described herein for processing a unit of whole blood into a concentrated red cell product and a plasma product.

FIG. 11 is similar to FIG. 9 but a somewhat more detailed view of components of a disposable fluid flow circuit or module and a durable controller module.

FIG. 12 is a schematic view of an alternate embodiment of the system according to the present disclosure in which the system is used for the separation of previously-collected whole blood.

FIG. 12A is a schematic view of a further alternate embodiment, similar to FIG. 12.

FIG. 13 is a perspective view of a two-pump blood separation system such as that shown in FIGS. 9, 11, 12 and 12A.

FIG. 14 is a schematic view of a further alternative similar to FIG. 12, except incorporating three pumps, illustrating the system in the priming phase.

FIG. 15 is a schematic view of the system of FIG. 14 illustrating the system in the separation phase.

FIG. 15A is a schematic view of a further alternative three-pump system, similar to FIGS. 14 and 15.

FIG. 16 is a schematic view of an automated whole blood collection system according to the present disclosure showing the configuration of the system for automated chairside collection and processing of whole blood from a donor in the priming mode.

FIG. 17 is a schematic view of the system of FIG. 16 showing the configuration of the system for collecting and separating whole blood into red blood cells and plasma.

FIG. 18 is a schematic view of the system of FIG. 16 showing the configuration of the system for rinsing the system with anticoagulant after the completion of blood collection from the donor.

FIG. 19 is a schematic view of the system of FIG. 16 showing the configuration of the system at the end of the blood collection procedure.

FIG. 20 is a schematic view of the system of FIG. 16 showing the configuration of the system in the optional arrangement for filtering the collected red blood cells through a leukocyte filter.

FIG. 21 is a schematic view of an alternate embodiment of an automated whole blood collection system to that of FIGS. 16-20 in which the single-use disposable fluid circuit component comprises an integral leukoreduction filter as part of the draw line of the donor access device.

FIG. 22 is a schematic view of an alternative embodiment of the single-use disposable fluid circuit of FIG. 21 in which the leukoreduction filter is positioned in the draw line downstream from the entry point where anticoagulant is introduced into the whole blood.

FIG. 23 shows a disposable set useful in the washing of cells in accordance with the method disclosed herein.

FIG. 24 shows another embodiment of a disposable set useful in the washing of cells in accordance with an alternative method disclosed herein.

FIG. 25 shows an embodiment of the control panel of a device useful in the washing of cells in accordance with the method disclosed herein.

FIGS. 26-28 are flowcharts of the steps in the method cell washing disclosed herein.

FIG. 29 is a flow chart illustrating a data management method in accordance the present disclosure.

FIG. 30 is a schematic drawing of a data management system according to the present disclosure in combination with a collection container and a processing kit.

FIG. 31 is a flow chart illustrating the various steps comprising a method for data management in accordance with the present disclosure.

DETAILED DESCRIPTION

A more detailed description of the spinning membrane separator in accordance with the present disclosure and its use in various automated systems is set forth below. It should be understood that description below of specific devices and methods is intended to be exemplary, and not exhaustive of all possible variations or applications. Thus, the scope of the disclosure is not intended to be limiting, and should be understood to encompass variations or embodiments that would occur to persons of ordinary skill.

Turning to FIGS. 1 and 2, a spinning membrane blood separation or fractionation system, generally designated 10, is shown. Such a system 10 is typically used to extract plasma from whole blood obtained from an individual human donor. For ease of understanding, only the plasma separation device and the associated drive unit are shown, although it should be understood that such a separator forms part of a disposable system including collection bags, bags of additives such as saline or ACD, return bags, tubing, etc., and that there are also associated control and instrumentation systems for operation of the device.

The system 10 includes a generally cylindrical housing 12, mounted concentrically about a longitudinal vertical central axis. An internal member 14 is mounted concentric with the central axis. The housing and internal member is relatively rotatable. In the preferred embodiment, as illustrated, the housing is stationary and the internal member is a rotating spinner that is rotatable concentrically within the cylindrical housing 12. The boundaries of the blood flow path are generally defined by the gap 16 between the interior surface of the housing 12 and the exterior surface of the rotary spinner 14. The spacing between the housing and the spinner is sometimes referred to as the shear gap. A typical shear gap may be approximately 0.025-0.050 inches (0.067-0.127 cm) and may be of a uniform dimension along the axis, for example, where the axis of the spinner and housing are coincident. The shear gap may also vary circumferentially for example, where the axis of the housing and spinner are offset.

The shear gap also may vary along the axial direction, for example preferably an increasing gap width in the direction of flow to limit hemolysis. Such a gap width may range from about 0.025 to about 0.075 inches (0.06-0.19 cm). For example the axes of the housing and rotor could be coincident and the diameter of the rotor decrease in the axial direction (direction of flow) while the diameter of inner surface of the housing remains constant or the diameter of the housing increases while the rotor diameter remains constant, or both surfaces vary in diameter. For example the gap width may be about 0.035 inches (0.088 cm) at the upstream or inlet end of the gap and about 0.059 inches (0.15 cm) at the downstream end or terminus of the gap. The gap width could be varied by varying the outer diameter of the rotor and/or the inner diameter of the facing housing surface. The gap width could change linearly or stepwise or in some other manner as may be desired. In any event, the width dimension of the gap is preferably selected so that at the desired relative rotational speed, Taylor-Couette flow, such as Taylor vortices, are created in the gap and hemolysis is limited.

Whole blood is fed from an inlet conduit 20 through an inlet orifice 22, which directs the blood into the blood flow entrance region in a path tangential to the circumference about the upper end of the spinner 14. At the bottom end of the cylindrical housing 12, the housing inner wall includes an exit orifice 34.

The cylindrical housing 12 is completed by an upper end cap 40 having an end boss 42, the walls of which are nonmagnetic, and a bottom end housing 44 terminating in a plasma outlet orifice 46 concentric with the central axis.

The spinner 14 is rotatably mounted between the upper end cap 40 and the bottom end housing 44. The spinner 14 comprises a shaped central mandrel or rotor 50, the outer surface of which is shaped to define a series of spaced-apart circumferential grooves or ribs 52 separated by annular lands 54. The surface channels defined by the circumferential grooves 52 are interconnected by longitudinal grooves 56. At each end of the mandrel 50, these grooves 56 are in communication with a central orifice or manifold 58.

In the illustrated embodiment, the surface of the rotary spinner 14 is at least partially, and is preferably substantially or entirely, covered by a cylindrical porous membrane 62. The membrane 62 typically has a nominal pore size of 0.6 microns, but other pore sizes may alternatively be used. Membranes useful in the washing methods described herein may be fibrous mesh membranes, cast membranes, track etched membranes or other types of membranes that will be known to those of skill in the art. For example, in one embodiment, the membrane may have a polyester mesh (substrate) with nylon particles solidified thereon, thereby creating a tortuous path through which only certain sized components will pass. In another embodiment, the membrane may be made of a thin (approximately 15 micron thick) sheet of, for example, polycarbonate. In this embodiment, pores (holes) may be larger than those described above. For example, pores may be approximately 3-5 microns. The pores may be sized to allow small formed components (e.g., platelets, microparticles, etc.) to pass, while the desired cells (e.g., white blood cells) are collected.

The rotary spinner is mounted in the upper end cap to rotate about a pin 64, which is press fit into the end cap 40 on one side and seated within a cylindrical bearing surface 65 in an end cylinder 66 forming part of the rotary spinner 14. The internal spinner or outer housing may be rotated by any suitable rotary drive device or system. As illustrated, the end cylinder 66 is partially encompassed by a ring 68 of magnetic material utilized in indirect driving of the spinner 14. A drive motor 70 exterior to the housing 12 is coupled to turn an annular magnetic drive member 72 that includes at least a pair of interior permanent magnets 74. As the annular drive member 72 is rotated, magnetic attraction between the ring 68 interior to the housing 12 and the magnets 74 exterior to the housing locks the spinner 14 to the exterior drive, causing the spinner 14 to rotate.

At the lower end of the rotary spinner 14, the central outlet orifice 58 communicates with a central bore 76 in an end bearing 78 that is concentric with the central axis. An end bearing seat is defined by an internal shoulder 80 that forms a lower edge of a central opening 82. The central opening 82 communicates with the plasma outlet orifice 46. If the inner facing surface of the housing is covered entirely or partially by a membrane, a fluid collection or manifold may be provided beneath the membrane to collect plasma and direct it through a housing outlet (not shown).

I. Membrane Separator Design

In keeping with one aspect of the application, a spinning membrane separator is provided that provides for improved plasma flow rates with an acceptably low level of hemolysis in the retained blood. Various factors are known to affect the filtration flow rate through spinning membrane separators, including the speed of rotation, the size of the gap between the spinning membrane and the shell, the effective area of the membrane, the concentration of red blood cells (or hematocrit), and the blood viscosity. Previous practices in the design of spinning membrane devices have been largely empirical, aided to some extent by vague phenomenological descriptions of the effects of the various design parameters on performance and hemolysis. This has proved to be inefficient in terms of development time and technical resources spent.

In contrast, the parameters of the spinning membrane separator of the present application were determined based on quantitative differential models that take into account the local plasma velocity through the membrane and the local hemoglobin concentration. These differential models were integrated over the length of the device to provide a total plasma flow rate and plasma hemoglobin concentration at the outlet of the device.

The method included the operational inputs based upon the existing Plasmacell-C separator geometry and operating conditions, including donor hematocrit, inlet blood flow rate, rotational speed, and effective membrane area. Also factored in were the geometric inputs of rotor radius, the width of the annular gap, and the length over which the integration is performed. See Table 1 below. To obtain predicted values for hypothetical separators, rotor radius and filtration length were varied from about 1.0 to up to about 2.0 times the current Plasmacell-C values in increments of 0.05, providing a 21×21 design space grid for each output variable of interest. For all devices, the housing taper and the gap at the outlet were held constant, and the inlet gap and rotational speed were varied accordingly. Models were also developed which related blood viscosity and density to hematocrit, temperature, and anticoagulant concentration.

TABLE 1 Inputs for Model Calculations Parameter, units Value Inlet blood flow rate, ml/min 106 Inlet hematocrit, % 42 Temperature, ° C. 35 Citrate concentration, % 5.66 Filtration length, in 2.992 Rotor radius with membrane, in 0.5335 Inlet gap, in 0.0265 Outlet gap, in 0.0230 Effective membrane fraction 0.50 Width of membrane bonding area, in 0.18 Rotation speed, rpm 3600 Wall hematocrit, % 0.90 Red cell radius, μm 2.75 Red cell hemoglobin concentration, 335.60 mg/dL Density of plasma, g/cm³ 1.024 Density of packed red cells, g/cm³ 1.096 Viscosity of citrated plasma, cP 1.39

In one implementation of the method, outputs of plasma flow rate and hemoglobin concentration were obtained for various values of the rotor radius, the rotational speed, and the integration length. The results of the models are shown in superimposed contour plots of the outlet hematocrit and outlet wall shear stress (FIG. 3), the outlet hematocrit and the outlet plasma hemoglobin concentration (FIG. 4), and the outlet hematocrit and Taylor number (FIG. 5), all as a function of the relative filtration length and spinner radius. As used herein, “filtration length” is understood to be axial length of the central mandrel or rotor 50 from the beginning to the end of grooves or ribs 52. It generally represents the length of the membrane available for filtration. The “spinner radius” or “spinner diameter” is understood to be the radius or diameter of the rotor with the membrane attached. FIG. 6 shows the plasma hemoglobin results as a function of filtration length and spinner radius in a three-dimensional plot, showing the increase in hemoglobin with larger devices. These results were then evaluated to provide the best balance of high plasma flow rate with acceptably low levels of hemolysis.

The models indicated that the effective area of the membrane has the strongest positive influence on performance. Further, while increasing the membrane area by increasing the diameter of the rotor more positively impacts flow rates than increasing the membrane area by increasing the length of the rotor, it also increases the potential for hemolysis due to the increased velocity of the membrane, and thus the increase in shear forces in the gap.

Accordingly, the models predicted lengths and diameters for the rotor that would result in increased membrane areas whose use would also have acceptably low levels of hemolysis. Prototype separators (based on the results of the models) were made and tested to validate the results predicted by the models. Table 2, below, compares a current Plasmacell-C plasmapheresis device with two potential alternatives based on the models.

TABLE 2 Device Parameter, units Plasmacell-C RL 140-162 RL 140-185 Relative filtration length 1.00 1.62 1.85 Relative spinner radius 1.00 1.40 1.40 Relative spinner speed 1.00 0.70 0.75 Filtration length, in 2.992 4.847 5.535 Spinner radius, in 0.5335 0.7469 0.7469 Spinner speed, rpm 3600 2520 2700 Inlet gap, in 0.0265 0.0287 0.0295 Outlet gap, in 0.0230 0.0230 0.0230 Inlet flow rate, ml/min 106 106 106 Inlet hematocrit, % 42 42 42 Citrate concentration, % 5.66 5.66 5.66 Plasma flow rate. ml/min 36.33 47.42 50.57 Outlet hematocrit, % 63.90 76.00 80.32 Outlet plasma hemoglobin 5.04 14.36 27.84 concentration, mg/dL Residence time, s 2.98 7.99 9.77 Centripetal pressure, mmHg 100.22 96.25 110.50 Torque, in-oz 1.48 4.70 6.29 Outlet Taylor number 89.07 51.00 46.96

With reference to Table 2 and FIG. 7, a spinning membrane separator 10 includes a rotary spinner 14 which has a spinner diameter D, a filtration length FL, and an overall length LOA. In a typical plasmapheresis device, such as the Plasmacell-C separator, the rotor has a diameter D of approximately 1.1″, a filtration length FL, of approximately 3″, and an overall length, LOA, of approximately 5.0″.

In accordance with the present application, it has been found that the diameter of the membrane can be increased by up to about 2.0 times the diameter of the membrane found in a typical plasmapheresis device, while the length can be increased up to about 2.5 times the length of the spinning membrane in a typical plasma pheresis device. An increase in the rotor size within these perimeters increases the filter membrane area sufficient to provide for a high plasma flow rate, while providing for an acceptably low level of hemolysis. In a specific example, a spinning membrane separator according to the present application may advantageously have a diameter D of 1.65″, a filtration length FL of 5.52″, and an overall length LOA of 7.7″.

Prototype spinning membrane separators were tested with bovine and human blood to validate the results predicted by the models. Blood flow rates of 100 ml/min were obtained with spinner speeds varying from 1000-3500 rpm. Outlet hematocrit levels of 80% and higher were obtained before high levels of fouling of the membrane were experienced. Collection times for 880 ml of plasma ranged from between approximately 18 and 20 minutes.

As noted above, the residence time of the red blood cells in the shear gap has a direct relationship to the amount of hemolysis. In spinning membrane separation devices, flow regions exist along the axial length of the rotor where the fluid flows is relatively stagnant, resulting in pockets of hemolysis. To the extent that red blood cells from the high hemolysis region intermix with the flow in the low hemolysis region, the quality of the collected red blood cells is degraded.

Accordingly, in keeping with another aspect of the application, a method is provided for creating separate fluid flow regions in the gap of a spinning membrane separator without the use of seals. The separate flow regions reduce or minimize the influence of mixing of the fluids between the two flow regions. The separate flow regions are achieved by having a raised rib or ridge in the gap to reduce or minimize the gap between the spinner and the outer cylinder. Preferably, the ridge or rib is provided on the surface of the rotor beyond where the spinning membrane is attached thereto.

The ridge is preferably located so as to define the boundary of the high perfusion flow region. The radial size of the ridge is inversely proportional to the decree of mixing allowed between the two regions defined thereby, with a larger radial dimension for the ridge allowing for less mixing. The axial dimension or extent of the ridge is also inversely proportional to the degree of mixing allowed, with a larger axial dimension allowing for less mixing. The axial dimension of the ridge is preferably at least one gap-size long to minimize the formation of adjacent Taylor vortices causing unwanted mixing.

With reference to FIG. 8, a schematic cross sectional representation of a spinning membrane separation device 10 is shown. The device comprises a fixed outer cylinder 12 and a rotating inner cylinder 14 having a filter member carried thereon. In accordance with the present application, the inner cylinder is provided with a radial ridge 90. This ridge serves to divide the gap 16 between the spinner and the outer housing into two fluid regions. A first fluid region 92 has a stagnant, non-perfused region of flow, typically on the portion of the spinner that extends beyond the filter membrane. A second fluid region 94, which typically contacts the filter membrane, has a highly perfused region of flow.

Because the first fluid region 92 is not perfused, blood residing therein is exposed to increased shear stresses for longer periods of time than the blood in the second fluid region 94. Thus, the blood in the first fluid region 92 may often become hemolyzed and has high concentrations of free hemoglobin (Hb). The ridge 90 inhibits fluid flow between the two fluid regions, thus minimizing the extent of mixing of the Hb-contaminated blood in the first region 92 with the low Hb blood in the second region 94.

While the ridge 90 is shown as being integral with the rotor, it could also be formed on the inside of the outer cylinder to achieve the same effect. As noted above, the axial dimension of the ridge should be at least one-gap size long. A typical spinning membrane separation device for performing plasmapheresis typically has a gap between the spinner and the containment wall of from 0.023″ to 0.0265″, and a ridge in accordance with the present application could have an axial dimension within the same general range. However, larger axial dimensions for the ridge will result in reduced mixing and, in one example, a rotor having a radially-extending ridge with an axial dimension of 0.092″ has been found to be effective.

II. Systems and Methods for Processing Previously Collected Whole Blood

A spinning membrane separation device as described above may be advantageously used in various blood processing systems and methods for which prior devices generally were not suited, particularly systems and process for obtaining Red Blood Cells. In one type of system and method, the spinner may be used for “back lab” processing of previously collected whole blood, as shown in FIGS. 9-15A.

Turning now to FIG. 9, a disposable fluid flow circuit or module A and a reusable durable controller or module B configured to cooperate with and control flow through the fluid circuit A are schematically illustrated. The disposable fluid circuit A as illustrated in FIG. 9 includes various components interconnected by flexible plastic tubing defining flow paths between the components. The circuit is preferably fully pre-assembled and pre-sterilized with the possible exception of the unit of whole blood container and the cell preservative container. More specifically, the illustrated disposable circuit in FIG. 9 includes whole blood container 101, a cell preservation solution container 102, blood component separator 108, plasma collection container 112, optional leukocyte reduction filter 113, and red cell collection container 115. While not illustrated in FIG. 9, the reusable module B may have hangers with associated weigh scales for supporting any or all of the containers 101, 102, 112 and 115. In various of the other embodiments discussed herein, such hangers/weigh scales may not be illustrated, but are understood to be part of the described systems.

The whole blood collection container 101 may be any suitable container but is typically a flexible plastic pouch or bag in which approximately 450 ml of whole blood have been previously collected. The container 101 may be part of a separate system during collection and then joined to the rest of the fluid circuit A or actually part of the circuit A at the time of collection. At the time collection, in accordance with customary procedure, the whole blood is mixed with an anticoagulant located in the primary container to prevent premature coagulation. Accordingly, “whole blood” as used herein includes blood mixed with anticoagulant.

Flexible plastic tubing 105 is attached to the whole blood collection container, such as by a sterile connection device or other suitable attachment mechanism, and defines a whole blood fluid flow path between the whole blood container 101 and a junction with cell preservative solution tubing 103, which extends from the cell preservation solution container 102 to the flow path junction. The flow path junction between the whole blood flow path and all preservative flow path is located at inlet clamp 116. From the junction, the flow path extends through tubing 107 to an inlet port in the separator 108.

As shown in FIG. 9 of this description, the separator housing has an outlet that communicates with the gap between the housing and rotor and with concentrated red cell flow path tubing 110 for withdrawing concentrated red cells from the separator gap. In addition, the housing includes an outlet from the rotor that communicates with the side of the membrane facing away from the gap (for example, the interior of the rotor) and communicates with plasma flow path tubing 111.

For reducing the number of leukocytes that may be present in the red cells, the disposable fluid flow circuit A optionally includes a leukocyte reduction filter 113, which may be of any suitable well known construction for removing leukocytes from concentrated red cells without unduly causing hemolysis of red cells or reducing the number of red cells in the collected product. The concentrated red cells flow from the leukocyte reduction filter 113 through a continuation 114 of the concentrated red cell flow path into storage container 15 which may be of any suitable plastic material compatible with red cell storage.

The reusable or durable controller module B, as shown in the FIG. 9 schematic, preferably includes a hematocrit sensor 104 for detecting the hematocrit and the whole blood flowing from the whole blood container 101. The hematocrit detector may be of any suitable design or construction but is preferably as described in U.S. Pat. No. 6,419,822, which is hereby incorporated by reference.

The durable reusable controller or control module B also includes an inlet clamp 116 which may be operated to control fluid from the whole blood container 101 or the cell preservative container 102 or, optionally, simultaneously and proportionally from both of the containers 101 and 102. For controlling flow of blood into the separator, the reusable module includes an inlet pump 106, which also may be of any suitable construction, and may be, for example, a peristaltic type pump which operates by progressive compression or squeezing of the tubing 107 forming the inlet flow path into the separator, a flexible diaphragm pump or other suitable pump. A pressure sensor 117 communicates with the inlet flow path between the pump 106 and the separator 108 to determine the inlet pumping pressure. The sensor may output to the control system to provide an alarm function in the event of an over-pressure condition or an under-pressure condition or both.

To control the flow rate of concentrated red cells from the separator 108, the reusable module also includes an outlet pump 109 that is associated with the outlet flow path 110, and functions in the manner similar to that described with respect to inlet pump 106. It also may be of any suitable construction such as a peristaltic pump, a flexible diaphragm or other suitable pumping structure. The plasma flow path 111 exiting the separator is preferably not controlled by a pump, and the volumetric flow rate through the plasma flow path tubing is the difference between the inlet volumetric flow rate from pump 106 and the outlet volumetric flow rate from pump 109. Reusable module B may, however, also include a clamp 118 for controlling flow of plasma through the plasma flow path tubing 111.

The disposable module A may also include a plasma collection container 112 in fluid communication with the plasma flow path for receiving plasma separated by the separator 108. Because the plasma passes through a porous membrane in the separator 108, the plasma that is collected in container 112 is largely cell free plasma and may be suitable for administration to patients, freezing for storage or subsequent processing.

FIG. 10 generally shows the flow path(s) of fluid through the system illustrated in FIG. 9. Specifically, it shows flow of whole blood from the single unit whole blood container 101 through the whole blood hematocrit detector 104, to a junction in the flow path located at the binary clamp 116. Cell preservation solution, such as a red cell preservation solution, flows from the red cell container 102 also to the junction at the binary clamp 116. Depending on the processing stage, the binary clamp allows the flow of whole blood or cell preservative downstream into the remainder of the system. Optionally, the clamp 116 could be a proportional clamp to allow a selected proportionate flow of whole blood and red cell preservative simultaneously.

From the binary clamp 116, the whole blood or cell preservative fluid flows through the inlet pump 106 and into the separation device 108. As explained earlier, the separation device employs a relatively rotating housing and rotor, at least one of which carries a membrane through which plasma is allowed to pass. In one embodiment, the membrane is carried on the surface of the rotor and plasma passes through the membrane and through internal passage labyrinth within the rotor exiting eventually to the plasma collection container 112. When the membrane is mounted on the rotor, the device is commonly referred to a spinning membrane separator, as shown in FIG. 10. However, it should be recognized that the membrane could potentially be mounted on the inside surface of the housing, facing the gap between the inside surface of the housing wall and the outer surface of the membrane, or a membrane could be carried on both the outer surface of the rotor and the inner surface of the housing so that plasma flows through membranes simultaneously, therefore potentially increasing the separation speed or performance of the separator 108. From the separator 108, the concentrated red cells flow through the housing outlet communicating with the gap between rotor and housing and through the red cell flow path 110 and the outlet pump 109, which controls the volumetric flow rate of the concentrated red cells.

While the hematocrit of the concentrated red cells removed from separator 108 may vary, it is anticipated that the hematocrit of the concentrated red cells will be approximately 80-85%. The outlet pump 109 pumps the concentrated red cells into the red cell collection container 115 and, optionally, through a leukocyte reduction filter located in the red cell flow path between the pump 109 and the collection container 115. The force of the pump pushing the concentrated red cells through the leukocyte reduction filter helps to maintain the processing time within a reasonable range, as compared, for example, to the time it would be required for gravity flow of concentrated red cells through a leukocyte reduction filter in a manual setting.

The plasma separated by the separator 108, as shown in the FIG. 10, flows from the separator device, for example, from an outlet communicating with a labyrinth of passageways within the rotor through a single control clamp 118 and to the plasma collection container 112. As noted earlier, because the plasma passes through the membrane, it is largely cell free and suitable for subsequent administration to patients, freezing, and/or for the processing, such as by fractionation to obtain plasma components for use in other therapeutic products. The system could also include a filter such as a leukocyte reduction filter in the plasma flow line 111 if desired.

FIG. 11 illustrates one version of a potential system employing both a disposable fluid circuit module A and a reusable or durable controller module B. Although shown assembled, the fluid circuit module A and durable module B have separate and independent utility and may be used with other systems as well. As can be seen in FIG. 11, the disposable module A is conveniently mounted to the face of the reusable module B, which has associated hangars or supports, some of which may be associated with weight scales, for supporting the various containers of the disposable system. The disposable module is, as indicated earlier, preferably preassembled, and pre-sterilized. The cell preservative solution container may be pre-attached as part of the disposable system or may be added later, such as by a sterile connection device or other suitable attachment. The whole blood container which contains the unit of previously collected whole blood may also be pre-attached to the pre-assembled fluid circuit or attached by way of a sterile connection device or other suitable attachment mechanism.

The face of the reusable module B includes, in this embodiment, a separate solution clamp 116 a for controlling flow of cell preservation solution from the solution container 102, which is hung from an elevated solution support pole. The whole blood container 101 is hung from a weight scale. The weight scale may be of conventional construction and may provide a weight measurement signal that may be used by the control system of the module B for sensing the amount of whole blood that remains in the container and/or the amount of whole blood that has been processed through the system. The disposable system includes a red cell flow path 105 that extends from the whole blood container, through the hematocrit detector 104, and through a separate whole blood clamp 116 b for controlling flow of whole blood from the container into the system. The cell preservative solution flow path 103 and the whole blood flow path 105 combine at a junction, such as a v-site or y-site, upstream of the inlet pump 106. The combined flow path extends through the inlet pump and to an inlet on the separator device 108. As is visible in FIG. 11, the reusable module B includes a drive unit, such as a magnetic drive unit for causing rotation of the rotor within the separator housing without requiring drive members or components to physically extend through the housing. In this arrangement, the rotor includes a magnetically coupled drive element that is rotated by the magnetic drive unit associated with the reusable module. This system is described more fully in U.S. Pat. No. 5,194,145 to Schoendrofer, incorporated by reference herein.

The concentrated red cell outlet from the separator 108 is attached to the red cell flow path 110, which extends through outlet pump 109 and to an inlet into the optional leukocyte reduction filter 113. Filter media located between the inlet and outlet of the leukocyte reduction filter substantially removes leukocytes from the red cells. From the filter outlet, the red cell flow path tubing 114 conveys the red cells into the red cell collection container 115.

Plasma is conducted from the plasma outlet of the separator through a plasma flow control clamp 118 and into the plasma collection container 112. In a manner similar to the whole blood container, the concentrated red cell container 115 and the plasma container 112 are suspended from weight scales which may be in electronic communication with the control system of the durable or reusable module B to provide information regarding the amount of concentrated red cells and/or plasma collected from the whole blood or the rate of collection.

While this system has been illustrated with certain basic components and features as described above, this description is not intended to preclude the addition of other components, such as sensors, pumps, filters or the like as may be desired. For example, it may optionally be desired to filter plasma before it enters the plasma collection container or to omit a leukoreduction filter for red cells. Although the plasma removed from the separator 108 is largely cell free, there may be a further desire to filter the plasma for reasons of subsequent administration or processing. The present description is not intended to preclude the possible addition of further components or the deletion of one or more of the components described above.

Turning now to the processing of whole blood in the illustrated system, the separation process begins by priming the system. “Priming” refers to the method by which the filter membrane is prepared (i.e., wetted) prior to use. Wetting with a fluid helps to displace air present in the matrix of the membrane prior to pressure-induced fluid flow through the membrane. Typically, a low viscosity non-biological fluid, such as a cell preservation solution (red cell solution such as, Adsol® solution) is used for wetting to allow the most effective displacement of air. During the prime, fluid is removed from the cell preservation solution bag 102 by the inlet pump 106 until the solution line 103, whole blood line 105, inlet line 107, and spinning membrane device 108 are completely filled with the solution. To ensure proper priming, the inlet pump 106 may move both clockwise and counterclockwise during the prime. The purpose of the solution prime is to prevent an air-blood interface from forming by creating a solution-blood interface and to wet the membrane within the separation device. Each is a measure taken to reduce the hemolysis of red blood cells.

After the system is successfully primed, the cell solution flow path 103 will be closed by the inlet clamp 116. The illustrated inlet clamp is a binary clamp that can close either the cell preservation solution flow path 103 or the whole blood flow path 107. Whole blood will then be pumped through the whole blood flow path 105 and the inlet flow path 107 by the inlet pump 106 into the separator 108. Inlet pump 106 flow rates can vary from about 10 ml/min to 150 ml/min depending on desired product outcomes for a specific procedure. As the whole blood leaves the whole blood container 101 it will pass through the whole blood hematocrit detector 104 which will generate an estimation of the whole blood hematocrit through IR LED reflectance measurements. Details of the hematocrit detector are explained in U.S. Pat. No. 6,419,822 (Title: Systems and methods for sensing red blood cell hematocrit), incorporated by reference. The whole blood hematocrit value is required for an initial control algorithm of the illustrated system, but may not be essential in other systems.

After whole blood has filled the separator 108, the system will begin to draw plasma from the separator which separates the whole blood entering the spinning membrane device into a red cell concentrate and virtually cell free plasma. Packed red blood cells at approximately 80-85% hematocrit will be pumped out of the separator 108 through the red cell flow path 110 and into the red blood cell leukofilter 113 by the outlet pump 109. The outlet pump forces the packed red blood cells through the red blood cell leukofilter 113 and the red cell concentrate which exits the red blood cell leukofilter 13 through the red blood cell line 114 and into the red blood cell product bag 115 will be successfully depleted of white blood cells and also depleted of platelets. It is also possible to complete a whole blood automated separation without the use of a red blood cell leukofilter 113. In this case the red blood cell leukofilter 114 would be removed from the system and the red blood cell product 115 would not be depleted of white blood cells or platelets.

Throughout the procedure, plasma will flow through the plasma flow path 111 into the plasma bag 112 at a flow rate equal to the difference between the inlet pump 106 flow rate and outlet pump 109 flow rate as is currently done in other spinning membrane separation applications like that applied in the Autopheresis-C® instrument sold by Fenwal, Inc. The pressure across the membrane generated by the offset in flow rates is monitored by the pressure sensor 117. The pressure measurements are used to control the plasma flow rate using the algorithm described in U.S. patent application Ser. No. 13/095,633, filed Apr. 27, 2011 (Title: SYSTEMS AND METHODS OF CONTROLLING FOULING DURING A FILTRATION PROCEDURE) hereby incorporated by reference.

The system in FIGS. 9-11 will continue to separate packed red blood cells and plasma until the whole blood bag 101 is empty as detected by air passing through the whole blood hematocrit detector 104. At this point the whole blood line 105 will be closed and the cell preservative solution line will be opened by the inlet clamp 116 to start the solution rinse or flush. During the solution rinse, preservative solution will be removed from the solution bag 102 and pumped into the separator 108 by the inlet pump 106. The plasma flow path 111 is closed by the plasma clamp 118 during the solution rinse. The solution rinse is used to flush any blood remaining in the system into the red blood cell product container 115. The solution rinse will also increase the red blood cell product container 115 volume to the level desired for proper red blood cell storage. After the solution rinse is finished the separation of the whole blood unit is complete.

Turning to FIG. 12, a further alternative two-pump system is shown. This embodiment differs from that in FIG. 9 primarily in that the fluid from the blood cell preservative solution is added after the red blood cells have been separated from the whole blood. More particularly, a container/bag 101 containing previously-collected whole blood (preferably already combined with an anticoagulant) is connected to the disposable system A through tubing segment 107 that leads to the blood separator 108. Pump 106 cooperates with tubing 107 to pump whole blood to the separator 108. Container 102 containing the red blood cell preservative additive solution is connected to the collection container 115 for the separated red blood cells through tubing 114, through which the separated red blood cells are also directed to container 115 through the leukocyte filter 114.

Sterile connection of the containers 101, 102 to the disposable system may be accomplished by a number of different ways. Container 102 for the additive solution may be supplied as part of the disposable system A, and may be joined to the remainder of the disposable (after sterilization by, e.g., gamma or E-Beam processing) during final packaging after the remainder of the disposable has been sterilized (by, e.g., moist heat processing). Alternatively, the container 102 may be formed integrally with the remainder of the disposable. In a further alternative, both the container 102 and the whole blood container 101 may be separate from the remainder of the disposable and connected at the time of use through, e.g., sterile spike connections 170, shown schematically in FIG. 10. Such spike connections preferably include a 0.2 micron filter to maintain sterility.

In another aspect of this embodiment, the tubing 103 connecting the additive solution container 102 to the leukocyte filter 62 may also be cooperatively engaged by the pump 109. Specifically, pump 109 may be a dual pump head that flows both the additive solution and the red blood cells exiting the separator 108 to control the flow rate of each based upon the inside diameter of the tubings 103 and 110.

The embodiment of FIG. 12 also utilizes an additional pressure sensor 117 b to monitor the back pressure from the leukocyte filter 113. Should the back pressure become excessive, as in the event of filter occlusion, the sensor will act to control the flow rate in order to ensure that the disposable does not rupture due to excessive pressure.

III. Membrane Priming

In keeping with another aspect of the disclosure, a method for priming a membrane filter is provided by which is more likely that the maximum amount of the surface area of the filter membrane is wetted, thus maximizing the membrane area available for filtration/separation. Specifically, when a spinning membrane filter system is primed as described above, with the spinning membrane oriented so that the axis of rotation is substantially vertical, the wetting solution enters at the top inlet port of the spinning separator, and gravity pulls the fluid toward the outlet at the bottom of the separator. Under such circumstances, the surface tension of the priming fluid will form an air-fluid interface that may move unevenly across the membrane surface, creating disruptions. The result is that certain areas of the filter membrane may not be wetted during priming, thus increasing the potential for air being trapped in the membrane matrix. The unwetted area of the membrane then becomes unavailable for separation, adversely affecting the separation efficiency of the membrane, until sufficient pressure is generated to displace the air.

Accordingly, a method for priming a membrane separator is provided that more uniformly wets the membrane surface by providing a more uniform air-fluid interface during priming. To this end, priming fluid is introduced into the separator so that it works against the force of gravity as the fluid-air interface advances in an upward direction across the surface of the membrane. This helps to ensure a more uniform wetting of the membrane, as the air displaced during priming is able to move in a single direction without being trapped as the air-fluid interface advances across the membrane.

Thus, according to this alternate method for priming, the priming fluid is introduced into the separator through a port at the bottom of the separator. The priming solution advances upwardly in the housing of the separator against the force of gravity to wet the surface of the membrane, with the air being expelled from the separator through a port at the top of the separator. While this “bottom to top” priming is described in the context of a spinning membrane separator, it is also applicable to any type of membrane separator that requires fluid priming prior to use.

With reference to FIGS. 9 and 12, the separator 108 is oriented vertically, so that the membrane separator and housing are relatively rotatable to one another about a generally-vertical axis, with the port for receiving the whole blood at the top of the separator and the ports through which the separated RBCs and plasma exit at the bottom of the separator. Thus, according to one way for performing this alternative priming method, and with reference to FIGS. 1 and 2, the priming solution may be introduced through one of the exit orifice 34 or plasma outlet orifice 46 of the spinning membrane separator 10, while air is expelled through the inlet orifice 22. According to another way for performing this alternative priming method, separator 10 may be inverted or upturned for priming, so that the exit orifice 34 and plasma outlet orifice 46 are at the top of the separator 10, and the inlet orifice 22 is at the bottom of the separator 10. The priming solution may then be introduced through the inlet 22, with the fluid-air interface advancing upwardly and air being expelled through either or both of the exit orifice 34 and the plasma outlet orifice 46. After priming, the separator 10 may be returned to its original orientation, with the inlet orifice 22 at the top and the exit orifice 34 and plasma outlet orifice 46 at the bottom.

A further alternative in which the “bottom to top” priming of the blood separator 108 described above may be used is shown in FIG. 12A. In contrast to FIG. 12, the inlet line 107 for the whole blood connects to the lower port of the separator 108 (to which the outlet line 110 had been attached in the embodiment of FIG. 12), while the outlet line 110 is connected to the port at the top of the separator 108 (to which the inlet line 107 had been attached in the embodiment of FIG. 12). To prime the system of FIG. 12A, clamp 116B is opened and pump 106 activated to flow whole blood (preferably with anticoagulant added) through the inlet line 107 so that it enters the separator 108 through the port at the lower end of the housing. As the whole blood fills the separator housing, air is expelled through the top port, to substantially eliminate all air from the device, and the filter membrane is wetted.

After priming is completed, the system continues to operate as shown in FIG. 12A to separate the whole blood into plasma, received in container 112, and red blood cells, received in container 115. At the end of the separation procedure, the separator may be rinsed with additive solution from container 102.

Turning to FIGS. 14 and 15, a further alternative blood separation system according to the present disclosure is shown. The system of FIGS. 14 and 15 is similar to that of FIGS. 9, 11, and 12 except that the durable module B includes a third pump 119 for selectively flowing additive solution to either the separator 108 during the priming phase (as shown in FIG. 14), or to the separated red blood cells during the separation phase (as shown in FIG. 15). The system of FIGS. 14 and 15 also includes a further clamp 120 for selectively permitting or preventing flow of fluid (separated red blood cells and additive solution) through the leukofilter 113 and into the red blood cell container 115. Prior to priming, clamp 20 could briefly remain open and pump 109 could pump residual air from container 115 and filter 113, minimizing the amount of air remaining in container 115 at the end of the procedure. Like FIG. 12A, the system of FIGS. 14 and 15 employs bottom to top priming of the separator 108, except using additive solution for the priming fluid instead of whole blood. During priming of the system, as shown in FIG. 14, air from the disposable system A is pushed to the whole blood container 101.

During the separation phase, the system is operated as shown in FIG. 15. At the conclusion of the separation phase, additive solution is pumped to the separator 108 (as shown in the prime phase illustrated in FIG. 14) to rinse the separator.

Turning to FIG. 15A, a further alternative system is shown. The system of FIG. 15A is like that of FIGS. 14 and 15, in that the reusable component B comprises three pumps 106, 109, and 119. However, the system of FIG. 15A is similar to that of FIG. 12A, in that the inlet line 107 for the whole blood is connected to the port at the bottom of the separator 108, while the outlet line for the separated red blood cells is connected to the port at the top of the separator. Thus, the system of FIG. 15A, whole blood is used for priming the system, similar to the system of FIG. 12A.

IV. Data Management Systems and Methods

The system described herein can also incorporate data management solutions. Weight scales and the addition label printing devices to the system would allow users to obtain product weight labels directly from the separation system at the completion of the procedure. This eliminates manual weighing and recording of data used in current processing methods. The module B may include a suitable user interface, such as a touch screen, keypad or keyboard, as well as a scanner, to allow users to input information such as user donor identification number, blood bank identification, fluid circuit kit numbers, lot numbers, etc., which could also improve data management efficiency in blood manufacturing centers.

More specifically, and in accordance with another aspect of the present disclosure, a method is provided for automating the transfer of data associated with the whole blood collection container, as well as other pertinent information, to the processing circuit used for the subsequent separation of the whole blood and the final storage container or containers for such separated blood component or components. This method is illustrated schematically in the flow chart of FIG. 29, where a source container is provided (step 122), which typically contains a unit of previously-collected whole blood, although the source container may contain a previously-processed blood product. The source container typically has data associated with it relating to the identification of the donor and the collection time, place, etc., such data preferably being in a machine-readable format, such as a bar code or a RFID tag. This data is then retrieved and transferred (step 124), and then associated with the processing circuit and final storage containers (step 126).

Turning to FIG. 30, one possible system for the use of a data management system in accordance with the present disclosure is shown. A blood collection container 128 and a separate processing circuit 130 having three final storage containers 132, 134 and 136, are provided. During the collection of the whole blood, donor identification information is encoded and associated with the container for the collected whole blood. This may be done by manually placing a bar code label for the donor id onto the container label, container pin, or tubing. It may also be done by utilizing an RFID writer at the point of collection, transferring the donor ID from a collection scale or hand-held device onto an RFID tag attached to the collection container. The use of RFID permits a greater amount of information to be managed, including such data as container-type, expiration date, collection time, collection volume, nurse identification, collection site, and the like.

The automated data transfer between the collection container 128 and the processing kit 130/storage containers 132, 134, 136 may occur in the context of the sterile connection of the collection container 128 to the processing kit 130. For example, an electromechanical system that accomplishes the sterile connection of the whole blood collection container to the processing kit may be used. Such a system is disclosed in U.S. Provisional Patent Application Ser. Nos. 61/578,690 and 61/585,467 filed on Dec. 21, 2011 and Jan. 11, 2012, respectively, which are incorporated herein by reference. The sterile connect device may be free standing, as shown in the above referenced provisional applications, or integrated with the reusable module B described above. Alternatively, the data management system may be simply associated with the reusable module B, without a sterile connect device associated therewith. In any event, the sterile connection device or reusable module includes a programmable controller configured to automatically perform, or prompt the user to perform, the various steps of the data management method, as described in greater detail below.

The data management system 138 incorporates a processing unit, a screen 140 for providing information to the user (such as prompts and confirmations), a touch pad 142 to permit the user to input information, and a scanner/reader 144 for retrieving and transferring information between the collection container 128 and the processing kit 130. The system 138 also provides for the printing of bar code labels or transfer of data to one or more RFID tags associated with the processing kit. Turning now to FIG. 31, a flow chart generally illustrating the data management method is shown. The method includes loading the collection bag and processing kit onto the reusable module and/or sterile connect device (step 140). The data associated with the processing kit and the data associated with the collection container is retrieved (steps 142 and 144). As can be appreciated, the order in which these steps are performed is not critical. As noted above, this data may take the form of a bar code, an RFID tag or other form, the processing kit and its associated collection containers have the pertinent data from the collection container associated therewith. This may either take the form of printing bar code labels or writing data to an RFID tag (steps 146 and 148). The collection container and processing kit are connected, preferably in a sterile connect procedure (step 150), such connection occurring at a time during the sequence of the performance of the above-described steps.

The blood in the collection container is then processed (step 152). The processing kit/storage container information is then retrieved and verified against the collection container data (steps 154 and 156). After such verification, the storage containers may be disconnected from the collection container (step 158).

The system of the present disclosure assists the user in performing the steps described above in that it provides prompts and confirmations for the various steps. For example, if the identifying information is in the form of a bar code, the system prompts the user to scan the bar code ID of the processing kit and the donor ID of the collection container. The system will then print replicate bar code labels on a printer that is either integral to the system or attached to it, with the type and quantity of the labels being determined by the type of processing kit loaded. The system then prompts the user to apply the bar code labels to the final storage containers. After the system processes the blood into its components, the system prompts the user to scan the final component container bar code IDs so that the system may verify correct bar code information prior to detaching the storage containers from the collection container and processing kit.

If the identifying information is associated with an RFID tag, the system automatically scans the RFID tag on the collection container and then automatically reads the information on the RFID included on the processing kit. The system then automatically replicates the collection container information to the RFID tag or tags associated with the processing kit storage containers. After the system processes the blood into the components, according to the type of processing kit detected by the instrument, the system will read the RFID tag on the final component containers to permit verification of the identifying information prior to detaching the blood storage containers from the processing kit and collection container.

It is contemplated that the system may employ both bar code and RFID as redundant systems, and include some or all of the steps described above, as applicable. While the bar code scanner/RFID reader is described as being associated with the reusable module B, it could be a dedicated station physically separate from the processing machine itself, though linked through the data management software.

While this data management method has been described in connection with the collection of the whole blood in a container separate from the processing kit and storage containers, it may equally well be used in connection with a system or kit in which the collection container is integral with the processing kit and its storage containers. Further, the method may be used in connection with the processing of whole blood drawn directly from a donor, as described below, with the donor identification data being provided by the donor, and not a collection container, or in a cell washing procedure, with the identification data being associated with the source container.

V. Systems and Methods for Processing Whole Blood from a Donor

In accordance with another aspect of the present disclosure, the spinning membrane separator described above may be advantageously used in the single step or “chairside” collection and separation of whole blood into blood components. As described below, an automated whole blood collection system is provided that separates whole blood into a single unit of red blood cells and plasma simultaneously with the collection of whole blood from a donor. The system is intended to be a single pass collection system, without reinfusion back to the donor of blood components. The system preferably comprises a disposable fluid flow circuit and a durable reusable controller that interfaces with the circuit and controls fluid flow therethrough. The flow circuit is preferably a single use pre-sterilized disposable fluid flow circuit that preferably comprises red blood cell and plasma collection containers, anti-coagulant and red cell additive solutions, a separator and a fistula for providing a passageway for whole blood from the donor into the fluid circuit. The durable controller preferably comprises a microprocessor-controlled, electromechanical device with valving, pumping, and sensing mechanisms configured to control flow through the circuit, as well as safety systems and alarm functions, appropriate for a whole blood collection procedure.

The method of blood collection utilizing the system comprises performing a venipuncture on a donor and the withdrawing whole blood from the donor into the disposable circuit where it is manipulated by the instrument and the components of the fluid circuit to result in the whole blood being separated into the desired red blood cell and plasma components. The donor remains connected to the system throughout the procedure, and all fluids remain in the fluid path of the single-use kit until the procedure is completed. As a “single pass” system, whole blood preferably passes through the flow circuit one time only, and no blood component is returned to the donor.

The red blood cells resulting from the collection may not necessarily be process leukoreduced. However, leukoreduction by filtration may be achieved with a leukoreduction filter preferably integrated to the single use circuit or by the use of a separate processing circuit that is sterile-connected to the red blood cell collection container.

The instrument preferably includes an operator interface for inputting information and/or displaying information such as a touch screen, keypad, mouse, keyboard, etc. A message display allows the operator to control the procedure, gather information on its status, and address any error conditions as they may arise.

Turning to the drawings, there is seen in FIGS. 16-19 a schematic representation of a whole blood automated collection system, generally designated 210, in accordance with the present disclosure, in different stages or phases of operation. The system preferably includes a reusable hardware component 212 that preferably comprises pumps, clamps and pressure sensors to control fluid flow, and a single-use pre-assembled sterile disposable fluid circuit component 214 that may be mountable to the hardware component and includes various containers/pouches, a donor access device or fistula, and a blood separation chamber, all interconnected by a sterile fluid pathway, such as flexible plastic tubing. The containers/pouches are typically collapsible, and made of a suitable plastic material, as is well known in the art. The material of the containers may differ depending on usage, and may include plasticizer-free materials such as DEHP-free polymers, particularly, but not exclusively, for red cell storage.

More specifically, the illustrated fluid circuit component or module 214 comprises a donor access device 216 that includes a first length of tubing 218 as the draw line through which whole blood is withdrawn from a donor and introduced into the fluid circuit 214. The donor access device 216 preferably comprises a needle, and particularly a small gauge needle (18-21 gauge) for enhanced donor comfort with a needle guard if desired for prevention of inadvertent needle sticks. The tubing 218 communicates with a blood separation device, generally designated 220 and, as described above, to introduce whole blood into the separator.

A second length of tubing 222 provides for fluid communication between the separator 220 and a first container/pouch 224 for receipt of the separated concentrated red blood cells, while a third length of tubing 226 provides for fluid communication between the separator 220 and a second container/pouch 228 for the receipt of plasma.

The fluid circuit 214 also comprises a source of anticoagulant (e.g., CPD), which is contained in a third container 230 that communicates with the first length of tubing 218 by means of a fourth length of tubing 232 that is joined to tubing 218 by, e.g., a Y-connector. The fluid circuit 214 may also include a source of preservative solution for the red blood cells that are to be delivered to the container/pouch 224. The preservative solution may be contained in a separate pouch that is communication with the container 224. Alternatively, the container 224 may be pre-filled with an amount of preservative solution adequate for the amount of red blood cells to be received therein during the collection procedure.

The fluid circuit 214 also includes an integral sampling system 234 for the aseptic collection of blood samples prior to and during the donation process. The sampling system 234 comprises a pouch that communicates with the first length of tubing 218 of the donor access device through a fifth length of tubing 236 upstream of the connection between tubing 218 and tubing 232, through which the anticoagulant is introduced. Tubing 236 preferably communicates with tubing 218 through a Y-connector or similar device.

The durable hardware component 212 preferably comprises a first pump 238 that cooperates with tubing 218 for pumping whole blood to the separation device 220 and a second pump 240 that cooperates with the tubing 222 for transporting substantially concentrated red blood cells from the separation chamber 220 to the first collection container 224. The pumps 238, 240 are preferably peristaltic or roller pumps that include a rotor with one or more rollers for compressing the tubing to force the fluid to be moved therethrough, although other suitable pump designs, such as flexible diaphragm pumps, may also be used. The hardware component also preferably includes a third pump 242 that cooperates with tubing 232 for transporting anticoagulant to the draw line tubing 218 through which whole blood is transported to the separator 220. The third pump 242 provides for metering the flow of anticoagulant, and also facilitates the priming and rinsing of the system, as will be described below. However, the third pump 242 is optional, and anticoagulant may be metered to the whole blood draw line 218 by gravity flow, with the tubing 232 being dimensioned to provide a suitable flow rate over the duration of the collection procedure.

The hardware component 212 also preferably comprises clamps 244, 246, 248 and 250 for selectively occluding and opening the tubing segments 218, 232, 222, and 226, respectively. The term “clamps” is used broadly herein, and includes any mechanism that cooperates with the flow paths, e.g., tubing segments, of the fluid circuit to selectively permit or preclude fluid flow therethrough. The hardware component 212 also preferably comprises pressure sensors 252, 254 in the draw line tubing 218 proximate or adjacent the needle (pressure sensor 252) and proximate or adjacent the inlet to the separator 220 (pressure sensor 254) to monitor the inlet pressure, such as to detect a vein collapse. A weigh scale (not shown) is also preferably provided for at least the first container 224 to provide feedback on the red blood cell volume collected.

In keeping with another aspect of the disclosure, the reusable hardware component preferably comprises a programmable controller 256 for actuating the pumps and clamps and monitoring the pressure sensors and weigh scales so that the whole blood collection procedure may be substantially automated. The controller 256 comprises a programmable microprocessor, and preferably includes an operator interface, such as touch screen and message display to allow the operator to enter and view data and control the procedure, gather information on its status, and address any “error” conditions that may arise.

To perform an automated collection and separation procedure with the automated blood collection system 210 thus far disclosed, the disposable fluid circuit 214 is loaded into operating position on the reusable hardware component 212 as shown in FIG. 16 of the accompanying drawings. In the phase or stage shown in FIG. 16, the system is primed with fluid to substantially remove air and wet the filter membrane. In the primary stage, the first clamp 244 is closed so as to prevent fluid communication between the donor access device 216 and the blood separation chamber 220, and anticoagulant is pumped via pumps 240 and 242 through the tubing 218, separator 212, and tubing 222 to prime the system. A venipuncture is then performed on the donor with the needle of the donor access device to admit whole blood into the tubing 218. At this point, the whole blood may be sampled by means of the sampling pouch 234.

Turning to FIG. 17, after priming, the first clamp 244 is opened to flow whole blood through the tubing 218 to the blood separator 220, via pump 238, to commence the collection/separation phase of the collection procedure. The anticoagulant continues to be metered into the draw line tubing segment 218 through tubing segment 232 by means of the third pump 242. Red blood cells exit the separator 220 through tubing 222. The fourth clamp 250 is opened so as to permit plasma to exit the separator 220 and to travel through the tube 226 to the second collection container 228. The first pump 238 presents the whole blood flow to the separator 220, with the inlet pressure being monitored by sensor 254, while the red blood cells are pumped from the separation chamber 220 by the second pump 240. The flow differential between the first pump 238 and the second pump 240 forces the separated plasma to exit the separator 220 into the second collection container 228.

With reference to FIG. 18, when the volume of the red blood cells in the first collection container 224 reaches a predetermined volume (as measured by the weight of the first collection container 224 as detected by the weigh scale), the weigh scale will provide the controller 256 with a signal that prompts the controller to terminate the collection procedure by closing the first clamp 244, thus occluding the draw line 218. The donor access device 216 may be withdrawn from the donor at this time. If the system is to be rinsed, the fourth clamp 250 is closed to occlude the flow line 226 to the second collection container 228 for the plasma. The first pump 238 is deactivated while the third pump 242 continues to deliver anticoagulant to the separator 220 with the anticoagulant being exhausted to the first collection container 224 through the tubing segment 222.

Turning to FIG. 19, at the conclusion of the rinse cycle, the second clamp 246 and third clamp 248 are closed, and the second pump 240 and third pump 242 deactivated.

At this point, the first collection container 224 containing the substantially concentrated red blood cells may be separated from the disposable fluid circuit 214 for storage or to facilitate leukofiltration. This may be done by simply hanging the collection container 224 and allowing gravity filtration of the red blood cells through a leukoreduction filter into a final storage container. However, in accordance with another aspect of the disclosure, and as shown in FIG. 20, a third collection container 258 may be provided that is in fluid communication with the second collection container 224 through a tubing segment 260, with the tubing segment 260 being in fluid communication with tubing segment 222 through a Y connector located on tubing segment 222 between the outlet of the separator 220 and the second pump 240. The third clamp 248 may then be opened to permit the flow of concentrated red blood cells out of the collection container 224, with the second pump 240 activated and pumping in the reverse direction to force the flow of concentrated red blood cells through the leukocyte reduction filter 262 and into the collection container 258. The pressure generated by pump 240 expedites the filtration process significantly as compared to gravity-fed leukofiltration of red cells.

As a further alternative, leukoreduction may be performed with respect to the whole blood during the draw phase of the operation. Turning to FIGS. 21 and 22, the draw line tubing 218 may include a leukocyte reduction filter 264 that is in line with the tubing 218. The filter 264 is located upstream of the first pump 238 so that the pump will exert a sufficient draw force on the blood to draw it through the filter 264 during collection. The leukofilter 264 may be located on the tubing segment 218 either upstream of where the anticoagulant is introduced into the system (as shown in FIG. 21) or downstream of where the anticoagulant is introduced into the draw line 218 (as shown in FIG. 22). Placement downstream of the anticoagulant junction allows the use of anticoagulant to flush any remaining whole blood from the filter 264 after the draw from the donor is completed. Also, placement of a leukoreduction filter in the draw line tubing 218 eliminates the need for a separate downstream leukoreduction filtration step, thus further streamlining the blood collection process.

The automated single-pass whole blood collection system and method described herein are expected to improve blood collection center efficiency, and decrease the operational costs, by accomplishing the separation of whole blood into red blood cell and plasma components without the need for subsequent manual operations. Further, the use of smaller-gauge needles in the donor access devices used with the system should enhance donor comfort, while the use of a draw pump allows the system to achieve donation times similar to typical whole blood collection. Additionally, by having the whole blood collection controlled by microprocessor, greater opportunities for data management are provided that are not typically found in current manual whole blood collection methods, including the use of integrated bar code readers and/or RFID technology, as described above.

In accordance with another aspect of the disclosure, methods, systems, and devices useful in the washing of biological cells, such as blood cells or other blood or biological components, are described below.

VI. Systems and Methods for Cell Washing

Biological cell washing may serve several purposes. For example, cell washing may be used to replace the liquid medium in which biological cells are suspended. In this case, a second liquid medium is added to replace and/or dilute the original liquid medium. Portions of the original liquid medium and the replacement liquid medium are separated from the cells. Additional replacement liquid media may be added until the concentration of the original liquid medium is below a certain percentage. Thereafter, the cells may be suspended in, for example, the replacement medium.

Cell washing may also be used to concentrate or further concentrate cells in a liquid medium. The cells suspended in a liquid medium are washed, such that a portion of the liquid medium is separated and removed from the cells.

Furthermore, cell washing may be used to remove undesired particulates, such as gross particulates or unwanted cellular material from a cell suspension of a particular size or “purify” a desired cell suspension or other liquid.

The method, systems, and apparatus described below may be employed to wash cells for any of the above-described reasons. More particularly, but without limitation, the methods, systems and apparatus described below may be used to wash blood cells such as red blood cells or white blood cells (leukocytes), or platelets.

In one particular embodiment, a suspension including white blood cells in a liquid culture medium may be washed to replace the liquid culture medium with another medium, such as saline, prior to use or further processing. The cell suspension including white blood cells in a liquid culture medium is delivered and introduced into a separator, such as a spinning membrane separator. The spinning membrane separator has a membrane filter with a pore size smaller than the white blood cells. In one embodiment, a liquid wash medium including the replacement liquid medium, such as saline, is also added to the separator to dilute the liquid culture medium. The separator is operated such that the liquids pass through the pores of the membrane and are extracted as waste. In this embodiment, as the liquid is extracted, the wash medium is added, such that the resulting cell suspension includes white blood cells suspended in the replacement liquid medium (e.g., the saline).

In another embodiment, the cell suspension may be concentrated (by removing supernatant) and collecting the concentrated cell suspension in a container of the processing set. Replacement fluid may be introduced into the separator, combined with the concentrated cells in the container and the cells then resuspended with the replacement fluid. If necessary, the resuspended cells/replacement fluid may be introduced into the separator to further concentrate the cells, remove supernatant, and resuspend the concentrated cells with additional replacement fluid. This cycle may be repeated, as necessary.

Similar processes may be used to wash red blood cells suspended in a liquid storage medium. The cell suspension including red blood cells suspended in a liquid storage medium may be washed to replace the liquid storage medium with another medium, such as saline, prior to use or further processing. The cell suspension is delivered and introduced into a separator, such as a spinning membrane separator. The spinning membrane separator has a membrane filter with a pore size smaller than the red blood cells. In one embodiment, a wash medium, i.e., replacement liquid medium, such as saline, may also be added to the separator to dilute the liquid storage medium. The separator is operated such that the liquid passes through the pores of the membrane and is extracted as waste. As the liquid is extracted, the wash medium is added, such that the resulting cell suspension includes red blood cells suspended in the replacement liquid medium (i.e., the saline). The wash and/or replacement liquid may also be a storage medium that includes nutrients and other components that allow for the long-term storage of the cells. Alternatively, in another embodiment, the red blood cells may first be concentrated and removed to a container, as generally described above. Replacement fluid may then be combined with the red blood cells in the container. The replacement fluid may be directly introduced into the container, or introduced into and through the separator and then into the container.

The systems, methods, and apparatus for cell washing described herein utilize a disposable set that includes a separator, such as a spinning membrane separator. The disposable set with the spinning membrane separator is mounted onto the hardware component of the system, i.e., separation device. The separation device includes clamps, pumps, motors, air detecting sensors, pressure transducer sensors, Hb detectors, weight scales, and a control logic/microprocessor included in a microprocessor. The control logic/microprocessor receives input data and signals from the operator and/or the various sensors, and controls the operation of the clamps, pumps and motors.

The cell suspension to be washed, i.e., cells suspended in a medium, may be provided in a sterile, disposable source container, which is connected, in sterile fashion, to the disposable set. A wash medium, such as saline or other suitable liquid, is also connected in sterile fashion or pre-attached to the disposable set. The control logic of the device operates the clamps and pumps to circulate the cell suspension through the tubing of the disposable set to the (spinning membrane) separator. The separation device, through its control system, also directs the wash solution through the tubing of the disposable set to the spinning membrane separator. The cell suspension and the wash solution may be mixed within the spinning membrane separator, may be mixed prior to entering the spinning membrane separator, or may be combined in a container after the cell suspension has been concentrated. Within the spinning membrane separator, the suspension medium is separated from the cells suspended therein. The suspension medium and remaining wash medium (if the suspension medium and wash medium have been combined) exits through a waste port, while the cells pass through a separate exit port.

If further washing and dilution is necessary, the washed cells may be re-circulated through the separator with an additional volume of the wash solution. In one embodiment, the cells that are to be “re-washed” may be transferred to one or more in-process containers, as will be described below. The control logic of the device operates clamps and pumps to circulate the cell suspension from the in-process container through tubing to an inlet of the spinning membrane separator or to an inlet of a second spinning membrane separator. Further wash medium is added, and the process repeats until an acceptable amount or concentration of the cells is achieved. The final cell suspension containing the cells is preferably collected in a final product container.

In accordance with the present disclosure, FIGS. 23-25 show exemplary systems useful in the washing of biological cells, such as, but not limited to, red blood cells and white blood cells. As noted above, the specific embodiments disclosed are intended to be exemplary and non-limiting. Thus, in one embodiment, the system described herein includes a disposable set 300 (FIG. 23 or 24) and hardware component or device 400 (FIG. 25). It will be appreciated that the disposable processing sets 300 shown in both FIGS. 23 and 24 are, in many respects, identical and common reference numerals are used in both FIGS. 23 and 24 to identify identical or similar elements of the disposable processing sets. To the extent that disposable processing sets differ in structure or in their use, such differences are discussed below. Disposable set 300 is mounted onto device 400 (FIG. 25), which is described in greater detail below.

As shown in FIGS. 23-24, separator 301 is integrated into the exemplary disposable set 300. Additionally, as will be described in greater detail below, disposable set 300 includes tubing, Y-connectors, in-process bag(s), sample pouch(es), final product bag(s), waste bag(s), and sterile filter(s).

The cell suspension to be washed is typically provided in a source container 302, shown in FIGS. 23 and 24 as disconnected from the disposable set. As noted above, source container 302 may be attached (in sterile fashion) at the time of use. Source container 302 has one or more receiving ports 303, 305, one of which may be adapted to receive spike connector 304 (FIG. 23) of disposable set 300. More particularly, source container 302 is connected to the disposable set 300 via the spike connector 304, which is connectable to access port 303. More preferably, however, source containers (and the fluid therein) may be free of a spike connector (as shown in FIG. 24) and accessed in a sterile manner by employing sterile docking devices, such as the BioWelder, available from Sartorius AG, or the SCD IIB Tubing Welder, available from Terumo Medical Corporation. A second access port 305 may also be provided for extracting fluid from the source bag 302.

As further shown in FIGS. 23-24, tubing segment 306 may optionally include a sampling sub-unit at branched-connector 308. One branch of branched-connector 308 may include a flow path 310 leading to sample pouch or site 312. Sample pouch or site 312 allows for the collection of a sample of the incoming source fluid. Flow to the sample pouch or site 312 is typically controlled by clamp 314. The other branch of branched-connector 308 is connected to tubing 316. Tubing 316 is connected to further downstream branched-connector 318. Branched-connector 318 communicates with tubing 316 and tubing 320, which provides a fluid flow path from in-process bag 322, described in greater detail below. Tubing segment 324 extends from one of the ports of branched-connector 318 and is joined to a port of further downstream branched-connector 326. A separate flow path defined by tubing 328 is also connected to a port of branched-connector 326. Tubing 328 may include an in-line sterile barrier filter 330 for filtering any particulate from a fluid before it enters the flow path leading to second branched-connector 326 and, ultimately separator 301.

In accordance with the system disclosed herein, a wash solution may be attached (or pre-attached) to set 300. As shown in FIGS. 23 and 24, tubing 332 (defining a flow path) preferably includes spike connector 334 at its end. Spike connector 334 is provided to establish flow communication with a container of a wash fluid, such as a disposable bag containing saline or other solution (not shown). The wash medium or fluid flows from the wash fluid source, through the second spike connector 334, through tubing segment 332, where it is filtered by the sterile barrier filter 330 described above, and then passes through tubing 328 to the input of the branched-connector 326 described above.

Tubing segment 336 defines a flow path connected at one end to a port of branched-connector 326 and to an inlet port of the separator 301. Preferably, in accordance with the present disclosure, separator 301 is a spinning membrane separator of the type described above.

As shown in FIGS. 23, 24 and 25, the spinning membrane separator 301 has at least two outlet ports. Outlet 646 of separator 301 receives the waste from the wash (i.e., the diluted suspension medium) and is connected to tubing 338, which defines a flow path to waste product container 340. The waste product container includes a further connection port 341 for sampling or withdrawing the waste from within the product container.

Separator 301 preferably includes a second outlet 648 that is connected to tubing segment 342. The other end of tubing segment 342 is connected to branched-connector 344, which branches into and defines a flow path to one or more in-process containers 322 and a flow path to a final product container 350. The final product container 350 may also include a sample pouch 352 (see FIG. 23) and an access port or luer connector 354. Sample pouch 352, shown with a pre-attached tube holder 352 in FIG. 23, allows for sample collection of the final product. Flow control to the sample pouch 352 is preferably controlled by clamp 356. The flow path through the access port 354 is controlled by clamp 358.

Turning now to the method of washing using the kit 300 of FIGS. 23 and 24, the disposable set 300 is first mounted onto panel 401 of the separation device (i.e., hardware) 400, shown in FIG. 25. Device 400 includes peristaltic pumps, clamps, and sensors, which control the flow through the disposable set. More specifically, control of the pumps, clamps and the like is provided by a software-driven microprocessor/controller of device 400. Tubing segments 362, 366 and 368 (shown in FIG. 23) are selectively mated with peristaltic pumps 402, 404, or 406 (shown in FIG. 25). (Waste line pump segment 368 may be relocated to separator outlet line 342, if desired.) Once the disposable set 300 is mounted onto the control panel 401 of device 400, the cell suspension in product bag 302 is attached, as previously described, by spike connector 304 or by sterile connection. A wash medium provided in a container (not shown) is likewise attached. In accordance with the operation of device 400, clamp 360 is opened and allows the cell suspension to flow from the product container 302.

Flow of the cell suspension is advanced by the action of peristaltic pump through the tubing 324 designated by the pump segment 362 and into the spinning membrane separator 301. Similarly, wash medium is advanced by the action of peristaltic pumps through the length of tubing 328 designated by the pump segment 366 with valves 362 and 364 in an open position. The wash medium flows through tubing 332, the sterile barrier filter 330, tubing 328, Y-connector 326, and into the spinning membrane separator 301. The wash medium and the cell suspension may be sequentially introduced into spinning membrane separator 301, allowing for mixing of the suspension and wash solution to occur within the chamber (gap) of separator 301 or in in-process container 322, as described below. Alternatively, the wash medium and cell suspension may be combined prior to introduction into separator 301 at (for example) the second branched-connector 326.

In yet a further alternative, cell suspension may first be introduced from source container 302 into separator 301, as generally described above. Cell suspension is concentrated within separator 301, allowing supernatant to pass through membrane, through outlet port 382, to waste product container 340. Concentrated cells exit separator 301 through port 384 and are directed to in-process container 322.

Once separation of concentrated cells from supernatant of the cell suspension is completed, replacement fluid is introduced from a replacement fluid container (not shown) into separator 301 (to flush out any residual cells) and is likewise directed through port 384 to in-process container 322. The concentrated cells are resuspended in the replacement fluid within in-process container 322, as shown in FIG. 23. If additional washing is desired or required, the system may be pre-programmed or otherwise controlled to (re)introduce the resuspended cells/replacement fluid into separator 301, wherein the separation of concentrated cells from supernatant is repeated. The final cell product is collected in final product container 350, where it may be resuspended with additional replacement fluid.

Regardless of the sequence of cell suspension/wash solution introduction or the disposable set used, the spinning action of the device causes cells to separate from the remainder of the fluid in which it was suspended and/or from the wash solution. Preferably, the supernatant and the wash solution pass through the membrane while the desired cells are concentrated within the chamber of the separator. The waste resulting from the separation, which includes wash medium and supernatant medium, exits port 382 and flows through tubing 338 to waste product container 340. The flow of waste is controlled by peristaltic pump through a portion of tubing 338 designated by the pump segment 368 to the waste product bag 340.

As described above, the concentrated and separated cell suspension exits the second outlet 384 of the spinning membrane separator 301. If no further washing is required, the control system closes clamp 370 and opens clamp 372. The closing of clamp 370 prevents the washed cell suspension from flowing through the tubing 346 and directs it through tubing 348 to the final product bag 350. The final product container 350 has an input for receiving the separated and washed cell suspension. The final product container 354 is connected to a weight sensor 374. The separation device measures the weight 374 of the container to determine whether the volume of the collected cells in final product container 350 is in the acceptable range and, therefore, whether the washing cycle is complete.

If further washing of the separated cell suspension is desired or required, the control system of separation device closes clamp 372 and clamp 376 and opens clamp 370. The closing of clamp 372 prevents the cell suspension from flowing through the tubing 348 and directs it through tubing 346 to the in-process bag 322. The in-process bag 322 has an inlet for receiving the separated cell suspension. The in-process bag 322 is connected to a weight sensor 378. The control system of the separation device determines the weight as sensed by weight sensor to determine whether enough of separated cell suspension is present in the in-process bag 322 to conduct another wash cycle. If it is determined that enough of the suspension is present, and further washing is desired, the control system of the separator device opens clamp 376 to open and directs the diluted and separated cell suspension through the output of the in-process bag 322, through tubing 320, into branched-connector 318, and through an air detector sensor 380. The air detector sensor 380 detects air in the cell suspension which passes through tubing 324. The control and operation device measures the readings from air detector sensor 380 and determines the further processes to be taken.

The separated cell suspension which includes cells suspended in diluted suspension medium is then passed through the washing process again, as described above. The wash process may be repeated as many times as desired and preferably until the diluted and separated cell suspension has an acceptable remaining concentration of suspension medium. The final diluted and separated cell suspension is collected in the final product bag 350.

Alternatively, rather than repeatedly processing the fluid through a single in-process container, a “batch-type” processing procedure may be followed by using two or more in-process containers 322 (in combination with final product container 350).

The disposable processing set 300 of FIG. 24 is particularly well suited for such “batch-type” processing. In accordance with a cell washing procedure using disposable set 300 of FIG. 24, cells initially separated from the original suspension medium are removed from separator 301 and introduced into one of the in-process containers 322 a. Replacement fluid is introduced into container 322 a and the cells resuspended. Resuspended cells in container 322 a may then be introduced into separator 301 wherein they are separated from the supernatant. Concentrated cells exit through outlet 648 in separator 301 and are introduced into a fresh (second) in-process container 322 b. Additional replacement fluid may be introduced into in-process container 322 b, and the process repeated, if necessary, with a further fresh (third) in-process container (not shown). The final cell product is then collected in final product container 350, as described above.

In accordance with the “batch-type” cell washing method described above, tubing segments 370 a, 370 b and 320 a, 320 b may be associated with clamps (not shown) to control flow to and from multiple in-process containers 322 a and 322 b. Thus, for example, a clamp on line 370 a would be open, while a clamp on line 370 b would be closed so that cells exiting separator 301 are directed to (first) in-process container 322 a.

For additional washing, cells resuspended in the fresh replacement fluid from container 322 a are introduced into separator 301 where the cells are separated from the supernatant, as previously described. The control system of device 400 closes the clamp (not shown in FIG. 24) on tubing segment 370 a and opens the clamp (not shown in FIG. 24) on tubing segment 370 b to allow cells to flow into fresh (second) in-process container 322 b. After the final wash, clamps (not shown) on segments 370 a, 370 b, etc., are closed and clamp 372 (as shown, for example, in FIG. 23) is opened to allow collection of the final product in container 350.

FIG. 24 shows the front panel 401 of separation device 400; i.e., the hardware, which includes peristaltic pumps 402, 404 and 406. As described above, pump segments 362, 364 and 368 from the disposable set are selectively associated with peristaltic pumps 402, 404, and 406. The peristaltic pumps articulate with the fluid set of FIG. 23 at the pump segments 362, 364 and 368 and advance the cell suspension within the disposable set, as will be understood by those of skill in the art. The control and operation device 400 also includes clamps 410, 412, 414. Clamps 410, 412, 414, and 416 are used to control the flow of the cell suspension through different segments of the disposable set, as described above.

Device 400 also includes several sensors to measure various conditions. The output of the sensors is utilized by device 400 to operate the wash cycle. One or more pressure transducer sensor(s) 426 may be provided on device 400 and may be associated with disposable set 300 at certain points to monitor the pressure during a procedure. Pressure transducer 426 may be integrated into an in-line pressure monitoring site (at, for example, tubing segment 336), to monitor pressure inside separator 301. Air detector 438 sensor may also be associated with the disposable set 300, as necessary. Air detector 438 is optional and may be provided to detect the location of fluid/air interfaces.

Device 400 includes weight scales 440, 442, 444, and 446 from which the final bag, in-process bag, cell suspension bag, and any additional bag, respectively, may depend and be weighed. The weights of the bags are monitored by weight sensors and recorded during a washing procedure. From measurements of the weight sensors, the device determines whether each bag is empty, partially full, or full and controls the components of the control and operation device 200, such as the peristaltic pumps and clamps 410, 412, 414, 416, 418, 420, 422, and 424.

Device 400 includes at least one drive unit or “spinner” 448, which causes the indirect driving of the spinning membrane separator 301. Spinner 448 may consist of a drive motor connected and operated by device 400, coupled to turn an annular magnetic drive member including at least a pair of permanent magnets. As the annular drive member is rotated, magnetic attraction between corresponding magnets within the housing of the spinning membrane separator cause the spinner within the housing of the spinning membrane separator to rotate.

FIGS. 26-28 diagrammatically set forth the method of cell washing as disclosed herein. The steps described below are preformed by the software driven microprocessing unit of device 400 with certain steps performed by the operator, as noted. Turning first to FIG. 26, the device is switched on at step 500. The device conducts self-calibration checks 502, including the checking of the peristaltic pumps, clamps, and sensors. Device 400 then prompts the user to enter selected procedural parameters (step 504), such as the washing procedure to be performed, the amount of cell suspension to be washed, the number of washings to take place, etc. The operator may then select and enter the procedural parameters for the wash procedure (step 506).

The device (through the controller) confirms the parameter entry 506 and then prompts the operator to load (step 510) the disposable set. The operator then loads the disposable set (step 512) onto the panel of device 400. After installation of the disposable set, the device confirms installation as shown in (step 514).

After the disposable set is mounted, the device automatically checks to determine whether the disposable set is properly installed (step 516). After the device determines that the disposable set is properly installed, the controller prompts the operator to connect the cell suspension and wash medium (step 518). The operator then connects the wash medium (such as, but not limited to saline) (step 520) to the disposable set via a spike connector, as previously described. The operator then connects the cell suspension within a product bag (step 522) to the disposable set via a spike connector.

As shown in FIG. 27, after the cell suspension and wash medium are connected to the disposable set, the operator confirms that the solutions are connected (step 524). The device prompts the operator to take a cell suspension sample (step 526). The operator or the device then opens sample pouch clamp 528 to introduce fluid into the sample pouch (step 546). Once the sample pouch is filled, it is then sealed and removed (542) from the disposable set. The operator confirms (step 544) that a sample has been taken. Following the removal of the sample pouch, the disposable set is primed (step 546) for the wash process.

The controller of separation device then commences the wash process. The cell suspension to be washed is transferred from its container (e.g., 302 of FIG. 23) through the disposable set to the spinning membrane separator 301. Likewise, the wash medium is transferred from its source, through the disposable set to the spinning membrane separator 301. In a preferred embodiment, the original cells of the cell suspension are concentrated and/or collected in either an in-process bag (for further processing) or collected in a final product bag which is subsequently removed from the disposable set. If (further) washing or diluting of the cell suspension is necessary, the cell suspension in the in-process bag may be washed (a second time) with the same or different wash medium following the process outlined above. Prior to the conclusion of each wash cycle, the cell suspension volume or weight is measured and recorded (step 550). When the concentration of the cells to wash medium reaches an acceptable level the final product bag is filled.

As shown in FIG. 28, once the desired volume of the final product is collected, the control and operation device prompts the operator to sample and seal the final product bag (step 552). A sample pouch is attached to the final product bag. The operator then seals and removes from the disposable set the washed cell suspension in the final product bag (step 552). The final product bag is then agitated (step 556). The operator opens the sample pouch by removing a clamp (step 558). The sample pouch is allowed to fill (step 560). Once the sample bag is filled, the clamp is closed and the sample pouch is sealed and removed (step 562). The operator then seals the disposable set lines (step 564) and confirms that the product bag has been sealed and removed, a sample pouch has been filled and removed, and that the disposable set lines have been sealed (step 566). The control and operation device then prompts the operator to remove the disposable set, as shown in step 568. The operator then removes and discards the disposable set, as shown in step 570.

Thus, an improved spinning membrane separator and methods and systems for using such a spinning membrane are disclosed. The description provided above is intended for illustrative purposes only, and is not intended to limit the scope of the disclosure to any specific method, system, or apparatus or device described herein. 

1. A blood filtration device comprising: a generally cylindrical housing having an interior wall; an interior member mounted interior of the housing and having an external surface; the interior wall of the housing and/or the external surface of the interior member including a porous membrane spaced apart from the facing wall of the housing or surface of the interior member so as to define an annular gap therebetween; the housing and interior member being relatively rotatable; an inlet for directing whole blood comprising plasma and red cells into the annular gap; a first outlet for directing plasma passing through the membrane to a collection container; and a second outlet for directing from the annular gap the remaining blood components; wherein the membrane has a surface area sufficient to separate plasma at a flow rate resulting in the residence time of red blood cells within the annular gap being insufficient to cause undue hemolysis.
 2. The blood filtration device of claim 1 wherein the interior member has a diameter greater than the diameter of the inner member of prior art devices and/or a filtration length of greater than the filtration length of the inner member of a reference device.
 3. The blood filtration device of claim 1 wherein the inner member has a diameter of up to about 2.0 times the diameter of the inner member of the prior art and a filtration length of up to about 2.5 times the filtration length of the inner member of the reference device.
 4. The blood filtration device of claim 1 wherein the rotary spinner has diameter of about 1.65″ and a filtration length of about 5.52″.
 5. The blood filtration device of claim 1 further comprising a ridge extending from one of the interior wall of the housing or the external wall of the interior member so as to reduce the annular gap therebetween, the ridge defining separate flow regions for fluid introduced into the annular gap.
 6. A blood filtration device comprising: a generally cylindrical housing having an interior wall; an interior member mounted interior of the housing and having an external surface; the interior wall of the housing and/or the external surface of the interior member including a filter membrane spaced from the facing wall of the housing or surface of the interior member so as to define an annular gap therebetween; the housing and interior member being relatively rotatable; a ridge extending from one of the interior wall of the housing or the external surface of the interior member so as to reduce the annular gap therebetween, the ridge defining separate flow regions for fluid introduced into the annular gap.
 7. The blood filtration device of claim 6 wherein the ridge has an axial dimension of at least the size of the annular gap.
 8. A method of designing a blood filtration device including a porous membrane, the steps comprising: developing a model utilizing inputs obtained semi-empirically from an existing filtration device having a porous membrane of a specified dimension to obtain specified outputs; applying the model to filtration devices of varying dimensions to obtain predicted values for the specified outputs; reviewing the predicted values obtained for the specified outputs; and selecting a filter membrane surface area based on a comparison of the predicted values obtained by application of the model.
 9. The method of claim 8 wherein the selected membrane dimensions provides a membrane surface area that enhances one or more filtration characteristics.
 10. The method of claim 9 wherein the filtration device comprises an inner member having the filter membrane mounted thereto, the inner member being mounted for rotation relative to a generally cylindrical housing and spaced therefrom to define a blood recovering gap, the inner member having a diameter and a filtration length sufficient to allow filtration without undue lysis to red blood cells in the blood.
 11. The method of claim 10 wherein model is applied to filtration devices having varying dimensions for one or more of filtration length, inner radius of the shear gap and the radius of the rotor with the membrane attached.
 12. The blood filtration device of claim 2 wherein the inner member has a diameter of up to about 2.0 times the diameter of the inner member of the prior art and a filtration length of up to about 2.5 times the filtration length of the inner member of the reference device.
 13. The blood filtration device of claim 5 wherein the ridge has an axial dimension of at least the size of the annular gap. 